CN1460008A - Method and apparatus for superficial skin heat treatment - Google Patents
Method and apparatus for superficial skin heat treatment Download PDFInfo
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- CN1460008A CN1460008A CN00819955.8A CN00819955A CN1460008A CN 1460008 A CN1460008 A CN 1460008A CN 00819955 A CN00819955 A CN 00819955A CN 1460008 A CN1460008 A CN 1460008A
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
- A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
- A61B18/203—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser applying laser energy to the outside of the body
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
- A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
- A61B18/22—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
- A61B18/28—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor for heating a thermal probe or absorber
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00315—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
- A61B2018/00452—Skin
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00315—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
- A61B2018/00452—Skin
- A61B2018/0047—Upper parts of the skin, e.g. skin peeling or treatment of wrinkles
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
- A61B2018/1807—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using light other than laser radiation
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Abstract
A method and apparatus for depth controlled conductive heat treatment of superficial layers preferably biological tissue such as the epidermal layer is disclosed. The method of the invention is to press a thin radiation absorptive layer attached to a bulk substrate with low thermal diffussivity in direct (or indirect via a protective overcoat layer on the absorptive layer) in physical contact with the object surface to heat. The cross section area of the adsortion layer is typically 1cm2. The absorptive layers in firmly attached to an optically transparent bulk substrate that is cooled in a controlled manner in order to remove excessive heat from the absorbing layer and bulk controlled manner in order to remove excessive heat from the absorbing layer and bulk substrate.
Description
Technical field
The present invention relates to a kind of biological tissue epidermis heat-treating apparatus and method, preferably the heat treatment of epidermal area one horny layer, clear layer and granular layer and solidifying.It is to be used for multiple reason that the selective thermal of carrying out epidermal area is handled, such as inter alia removal wrinkle, impermanency remove hair, skin of face regeneration, enhancing and the psoriasis supplied with via the anesthetis of skin handle.
Background technology
Being used for the prior art that epidermal area solidifies, evaporates (evaporation) and excision is based on coherent laser illumination and organizes direct interaction.Yet, have only the lasing light emitter of a few types to be applicable to the tissue removal that the degree of depth is controlled.This problem is that the extinction depth of the optical maser wavelength in epidermal area must be in a few μ m in the tissue or the littler scope, absorbs with the surface of realizing laser.The most frequently used laser that is used for epidermal tissue's removal is respectively Er:YAG and the excimer laser that emission wavelength is 2940nm and 193nm.Corresponding extinction depth is 3～5 μ m (in water) and 0.1 μ m (in protein).Emission wavelength is that the carbon dioxide laser of 10.6 μ m also can be used for the tissue removal to a certain extent, but because bigger extinction depth 30～50 μ m (in water), have vesicle and hemorrhage problem in darker organized layer, this needs 2～6 months convalescent period.Even rare, but this also is the problem of Er:YAG laser.This reason can make an explanation by the following fact, that is, horny layer (thickness 15～30 μ m) mainly is made of the very low keratin of water content under normal operation.Extinction coefficient e=2940 μ m in keratin is obviously greater than 3～5 μ m in the water, and this can explain that these do not expect and unfavorable result.The only laser type that can carry out accurate and expected epidermal area removal is that emission wavelength is the excimer laser of 193nm.Excimer laser is very expensive, and is difficult to operation.The excimer laser of 193nm is applicable to not too also that the optical fiber by standard connects and transmits light beam that this is because very high based on the waveguide attenuation of vitreous silica (quartz) glass.Living cells is exposed to the radiating long-term effect of UV not to be studied fully.May there be the excessive risk that produces the cancer relevant with excimer laser.
With can be used for epidermal tissue on the bonded lasing light emitter principle of the contact probe that has radiation absorption layer and remove.The use that covers whole radiation absorption layers of a detecting probe surface part will be eliminated by all heat energy by transmit the problem of the extinction depth of bringing to tissue.
The contact probe that is used for laser aiming generally has very little effective area, generally only has several square millimeters.Exist multiple these surface-probes of supplying with laser that make to have the reason of so little surface area, important aspect is from the pulse energy of laser low being restricted of electrical efficiency owing to used laser, generally, only there is a few percent of laser pumping institute energy requirement to be converted into the laser irradiation energy.Therefore, the laser contact probe that has a radiation absorption layer is applicable to that not too larger area handles.
Be used for that another major issue relevant than the heat treated laser of large tracts of land is because the coherence of laser emission and inherent speckle and modulation (mod) pattern of forming.Even these phenomenons still exist after propagating by fiber waveguide.Laser emission by the round fiber guiding often shows the formed annular ring of the intensity pattern that has overlapping speckle.The waveguide of use other types cross-sectional geometries (as rectangle) can not weaken the problem of mode pattern.Thereby laser and combining of contact probe are not suitable for the processing on the big surface that utilizes the large tracts of land contact probe, and this is owing to be vital at even heating aspect this.Generally speaking, lasing light emitter is compared expensive a lot with the arc light source.Being used for other commonsense methods that surface skin removes is mechanical skin attrition and Chemopeel, and these all exist can not degree of depth control and the problem of predictability.
Summary of the invention
Generally speaking, the present invention is characterised in that the method for optionally solidifying and shrinking epidermal area, horny layer, clear layer and granular layer under the prerequisite of the organized layer below not serious damage.Method of the present invention contacts the heated probe that has radiation absorption layer based on skin surface.Absorbed layer is heated by the concentrated radiation from the incoherent arc light of pulse in a controlled manner.
Radiation absorption layer
What radiation absorption layer was firm also presses on the distal surface of the bulk substrate on the skin gently attached to forming the physics contact, so that form the even contact surface.Bulk substrate should be transparent on the whole radiation spectrum of radiation source.Radiation absorption layer is Fast Heating when being shone from the noncoherent radiation that converges of pulsed arc light modulation.To help the heating of absorbed layer by the whole emission wavelength spectra (being generally 0.2～2 μ m) of arc light generation.Have and the non-sensitivity of wavelength of arc light emission spectra coupling and the coating material of high absorption coefficient by selection, the major part of luminous energy will be converted into the heat in the absorbed layer.Thereby overall energy efficiency is compared with the lamp excitation laser and is able to obvious raising.Preferably be chosen as the multiple oxide that carbon or nickel, zirconium etc. are made for the material of absorbed layer with the high absorption coefficient in 0.2～3 mu m range.The thickness of absorbed layer should be in 1～50 mu m range, and is preferably in 2～10 mu m ranges, affine if the material composition of absorbed layer is not organized, and will need the protective coating (overcoat layer) of aluminium oxide or silicon oxide so.The general minimum of the thickness of protective layer is 1～5 μ m.
In order further to improve from the conduction of heat of detecting probe surface to skin, can be with very the liquid or the gel of thin layer are applied on the skin before handling with contact probe.The viscosity of this contacting with fluid must enough be hanged down to allow too much gel to extrude from the detecting probe surface contact area, and this is because the thickness of contact liq layer must be less than 5～15 μ m.The example of contact liq is water, saline solution or ultrasound wave contact gel.Described liquid can be based on silicone oil, or hyaluronic acid, and most preferred selection is the chemical compound made of water, denatured alcohol, propylene glycol, glycerol, sodium hydroxide, PEG40 castor oil hydrogenated, panthenol and carbomer and the gel mixture of lignocaine.Lignocaine is subcutaneous anesthesia gel, and will ease the pain in processing procedure.The degree of depth control of (solidifying) tissue of heat effect mainly realizes by the persistent period of regulating pulses of radiation and the radiating energy density of controlling on the absorbed layer.Radiant energy intensity is controlled by the discharge current of arc light by regulating.Energy level is applicable to that special optics geometry and detecting probe surface amass.The steady heating of absorbed layer by will being mixed by the fiber waveguide with the length that decuples the probe cross-sectional diameter at least and guaranteed from the light of arc light, and the probe cross-sectional diameter is generally 10mm.The cross section of waveguide is preferably 0.5～5cm
2, be preferably 1～2cm
2The circle of cross-sectional area and rectangle.
The typical pulse persistent period of lamp is in 0.1～500ms scope, and repetitive rate is generally 0.5～5Hz.
The heat effect degree of depth of hypodermic layer will be corresponding to the pulse length scope of 0.1～500ms, and according to Fig. 2, this degree of depth is 7～500 μ m.The distance of 10% point of tissue surface temperature rising that effectively being defined as of the heat effect degree of depth is inboard to tissue from (heated) surface, temperature raises when being approximately heating pulse and stopping.
Suppose that skin surface temperature just in time reaches 100 ℃ (so when heating pulse-pulse length 0.1～500ms-termination, water boiling and evaporation in the tissue), solidify the degree of depth accordingly and will be 2～127 μ m, promptly, temperature is 70～72 ℃ or the subcutaneous depth of eminence more, sees Fig. 4.
As with constant energy intensity (W/m
2) fundamental relation between the inboard Temperature Distribution of bulk health on surface of heating provides by following equation:
Temperature Distribution (1)
Wherein:
Thermal diffusivity (m2/s) (2)
Equation (1) is effectively for the one dimension hot-fluid, if the heat effect degree of depth much smaller than the cross sectional dimensions of surperficial thermal source, this can set up so.
The heated cross-sectional area z=of surface temperature paired pulses time (3) P=radiant power A=is apart from the heat conductivity apart from ě=material that is heated the surface
The thermal capacity T of the density c=material of p=material
0=T (z-0) s=2* (K*e ') (4) s=since thermal diffusion cause apart from the evenly heat operating distance z=on surface apart from below having provided of surface apart from Eq. (1) for the associated temperature rising (see figure 3) of the different value of z: z=0.5*s: the distance that has reached 35.4% surface of surface temperature apart from temperature; Z=s: the distance that has reached 8.9% surface of surface temperature apart from temperature; Z=2*s: the distance that has reached 0.2% surface of surface temperature apart from temperature.The gross energy of the heat pulse of per unit area is provided by following equation:
E＝P*e′ (5)
Equation (5) and equation (2) and (3) have provided the estimation for the pulse energy of the required per unit area of pulse length é.
The accompanying required gross energy of bulk substrate of heat tissue and absorbed layer provides following equation:
From equation (6), obviously as can be seen
To surface temperature T
OThe pulse energy influence required with the set-point of the persistent period é of heating pulse is bigger.Two of bulk substrate that are used for absorbing material mainly are chosen as sapphire and quartz glass, and this is because these two kinds of materials have good resistivity to thermal chokes (thermalchock), and transparent on the optics simultaneously.For tissue (water), quartz glass and sapphire item
Be 1530,1499 and 6734 (ius) accordingly.By these figure, be used for absorbed layer bulk substrate obviously be chosen as quartz glass, this is because required in this case pulse energy is compared with the sapphire of substrate as a whole only is 37%.
The heat energy that is dissipated in each heating pulse process in the bulk substrate layer must be drained before next pulse emission, otherwise, probe will be in the time before the next pulse emission preheating tissue.The preheating of tissue is undesirable.The preferred embodiment of hot zinc (heat zinc) is attached on the enough big sapphire host with higher thermal conduction characteristic for the uncoated side with bulk substrate (quartz).Sapphire preferably should utilize with the contacted Peltier's element of sapphire host and continue cooling.Sapphire host is positioned on the beam path.In a preferred embodiment, sapphire host is the far-end of fiber waveguide, that is, sapphire host and optical system are separated.If adhering to by rights of bulk substrate and sapphire host forms, it can form disposable use element.For example, can prepare with respect to the surface of absorbed layer has the stannum adhesive film, so that change bulk substrate easily when new processing begins.Disposable probe bulk substrate has prevented the propagation of Contagious disease between the individuality.
Preferably the thickness of the bulk substrate of being made by quartz should be in 10～1000 mu m ranges.Optimum thickness can calculate at specific pulse recurrence rate and pulse duration.
Description of drawings
More fully state the various features and the details of these and other purposes of the present invention and operation and structure hereinafter with reference to accompanying drawing, wherein:
Fig. 1 is used to implement schematic representation of apparatus of the present invention, in said apparatus, Reference numeral 1 indicates the Pulse Electric magnetic source, as the laser that converges by suitable optical system 2, Reference numeral 3 indicates waveguide, and 4 signs are attached to the bulk substrate on the waveguide outlet cross section.Element 5 is such as the unitary chiller of amber ear card;
Fig. 2 is the curve of the persistent period of the relative heating pulse of epidermis interior-heat depth of interaction;
Fig. 3 is the distribute curve of the inboard relative depth of relative whole human body of relative temperature;
Fig. 4 is the curve that solidifies the persistent period of degree of depth relative energy pulse in the epidermis;
Fig. 5 is the sketch map how device of Fig. 1 is used to handle epidermis.
The specific embodiment
With reference to Fig. 1 and Fig. 5, Reference numeral 1 indicates Pulse Electric magnetic source, preferably gas-discharge tube and laser instrument.Converged by utilizing suitable optical system 2 from the radiation that light source 1 sends.Comprise at electromagnet source under the situation of discharge lamp that the light of Chuan Boing is by utilizing the back reflection mirror system backward, for example the reflecting mirror of parabola or ellipsoid gives guiding once more towards fiber waveguide.If the size of light source is suitable for the geometric size of the inlet of waveguide 3, also can use the back reflection mirror of other types, such as white scattering pottery.When light source is laser instrument, converge optical system and generally comprise the lens arra system, thereby all enters in the surface along forwards converging to waveguide 3 ground as much as possible to the radiation of propagating.Waveguide enters outwardly, and the typical cross section area is 0.3～3cm
2
Waveguide 3 is preferably by having circle or rectangular cross section ground crystalline sapphire is made.Also can use other geometries, as ellipse.Selecting sapphire material in waveguide is because the higher thermal conduction characteristic of this material.Waveguide 3 suitable length are in 20～60mm scope.Bigger cross section needs long waveguide, and this is because except simple radiation guiding, the major function of waveguide is smooth radiation field from light source 1.Disposable bulk substrate 4 is attached on the outlet cross section of waveguide with skim radiation transparent optical glue 4.6, and this glue 4.6 is being grouped together of optical match liquid and the device that is used for the bulk substrate mechanical fixation.Complete bulk substrate should be able to be changed after individual Medical Treatment.The size of the cross-sectional geometry of bulk substrate 4 should form is a bit larger tham waveguide 3 corresponding cross sectional dimensions, to avoid radiation leakage.Bulk substrate 4 comprises a pieces of quartz glass 4.1 and a laminated coating, this coating comprises radiation absorption layer 4.2, be preferably the sputtering layer of the carbon of thickness 1～10 μ m or sull and nontoxic and organize affine layer, this layer preferably made by the crystalline sapphire of 0.2～2 μ m thickness.Be transmitted in the organized layer in order to improve heat, the contact brining layer of ointment or liquid should be on the hypodermic layer 4.5 of the epidermal area 6 that be applied to tissue 6 before the processing.The contact brining layer 4.4 that is made of ointment or liquid should have at least 100 ℃ boiling point, is preferably 150 to 250 ℃.If necessary, organize anesthetis can be included in ointment or the liquid, to be used for pain management.The undue heat that is produced by absorbed radiation in the layer 4.2 should be by being removed on the near-end that chiller is attached to waveguide 3.2.Chiller 5 should be for amber ear card unit or by the refrigerative metal master of circulating coolant.
Though described by means of its preferred embodiment in the above in this present invention, under the prerequisite that does not deviate from the marrow of the present invention that limits as appended claims and theme feature, can be improved.
Claims (35)
1. one kind is used for epidermal tissue's layer conductivity heat-treating apparatus and method, comprising:
(1) is used to produce the device of electromagnetic radiation;
(2) be used to converge described radiating device;
(3) be used for described electromagnetic radiation energy is converted into the device that approaches the heat in the absorbed layer;
(4) be used for the undue heat that effective cooling and absorbing layer produces and the device of pre-cooled skin corium; And
(5) be used at absorbed layer and want effective heat conducting device between the heated body surface.
2. device as claimed in claim 1 is characterized in that, the described device that is used to produce electromagnetic radiation energy is that impulse wave length is at least 0.1 μ m, and is the electric light of 500ms to the maximum.
3. method as claimed in claim 2 is characterized in that, this electric light is the gas discharge arc light.
4. method as claimed in claim 2 is characterized in that, electric light can produce 0.1～200J/cm on absorbed layer
2Luminous energy intensity.
5. the method for claim 1 is characterized in that, the described device that is used to produce electromagnetic energy is the laser instrument that pulse length is at least 1 μ s.
6. method as claimed in claim 5 is characterized in that, lasing light emitter is a high-power diode laser.
7. the method for claim 1 is characterized in that, the described device that is used for described electromagnetic energy is converted to heat comprises at least one radiation absorption layer, and this layer thickness is 0.1～1000 μ m.
8. method as claimed in claim 7 is characterized in that, described radiation absorption layer comprises that thickness is oxide and the carbon-coating of 0.5～50 μ m.
9. structure as claimed in claim 8 is characterized in that, described layer of oxide material is at least a oxide of making in the following element, and this element is: zirconium, aluminum, nickel, zinc, indium, strontium, barium, silicon.
10. structure as claimed in claim 7, it is characterized in that described a plurality of layers comprise that at least one has the optically transparent bulk substrate layer of low thermal diffusivity, this bulk substrate layer contacts with a side physics of described radiation absorption layer, and the thickness of bulk substrate is 1～1000 μ m.
11. structure as claimed in claim 10 is characterized in that, described bulk substrate is made by quartz glass.
12. structure as claimed in claim 10 is characterized in that, described bulk substrate is a disposable parts, and it is attached to bulk substrate by removable glue has on the fiber waveguide of identical cross-section geometry.
13. structure as claimed in claim 7 is characterized in that, is under the non-situation of organizing affine composition at absorbed layer, described a plurality of layers comprise the coating that is attached on the absorbed layer tissue sides.
14. structure as claimed in claim 13 is characterized in that, described coating is by organizing affinitive material to make.
15. structure as claimed in claim 14 is characterized in that, described layer by thickness be 0.1～10 μ m, the crystalline solid (sapphire) or the polycrystalline aluminum oxide (aluminium oxide) that are preferably 0.5～2 μ m make.
16. structure as claimed in claim 7 is characterized in that, the geometry of described absorbed layer is 0.1～5cm
2The circle of area or rectangle.
17. structure as claimed in claim 1 is characterized in that, the described device that is used to converge described electromagnetic energy comprises optical element, and wherein at least one is that refraction/diffraction optical element and/or at least one are reflective optical devices.
18. device as claimed in claim 1 is characterized in that, described being used for comprises the fiber waveguide that at least one conducts described electromagnetic energy to absorbed layer at a distance with the device that described electromagnetic energy pools heat.
19. device as claimed in claim 18 is characterized in that, described fiber waveguide is based on the dielectric waveguide of at least a following waveguide material, and this material comprises: mix or unadulterated quartz glass, crystalline sapphire, flint glass or crown glass.
20. device as claimed in claim 18 is characterized in that, described fiber waveguide at least topical application with the metal level of high reflectance, as gold, aluminum or silver.
21. structure as claimed in claim 18 is characterized in that, the distal portions of described optical waveguide systems is made by optically transparent material, and this material has higher thermal conduction characteristic and diffusibility, and a side of described waveguide contacts with described bulk substrate physics.
22. structure as claimed in claim 21 is characterized in that, the described distal portions of fiber waveguide is made by crystalline sapphire glass.
23. structure as claimed in claim 21 is characterized in that, the distal portions of described fiber waveguide is made by crystalline sapphire glass.
24. device as claimed in claim 1 is characterized in that, the described heat that is used for producing in the absorbed layer effectively is transmitted to gel or the liquid that the lip-deep device of biological tissue comprises proper viscosity and boiling point.
25. structure as claimed in claim 24 is characterized in that, described ointment or liquid are based on silicone oil.
26. structure as claimed in claim 24 is characterized in that, described ointment or liquid are based on hyaluronic.
27. structure as claimed in claim 24 is characterized in that, described ointment or liquid comprise the anesthetis that is used to pass skin deposits.
28. structure as claimed in claim 24 is characterized in that, described ointment or liquid are based on water or normal saline solution.
29. structure as claimed in claim 24 is characterized in that, described ointment or liquid comprise organizes anesthetis.
30. structure as claimed in claim 24 is characterized in that, the boiling point of described gel or liquid is 75～400 ℃, is preferably 150～300 ℃.
31. structure as claimed in claim 1, it is characterized in that, the described undue heat effective refrigerative device from accompanying absorbed layer that is used for bulk substrate is produced comprises the radiator that contacts with described bulk substrate physics, and this bulk substrate is adhered to absorbed layer at its opposite side.
32. structure as claimed in claim 31 is characterized in that, described radiator comprises amber ear card chiller.
33. structure as claimed in claim 31 is characterized in that, described radiator comprises having the main body that allows cooling liquid circulation inner passage.
34. structure as claimed in claim 31 is characterized in that, described hot zinc is cooled to-20 to+20 ℃ of temperature in the scope with described bulk substrate layer.
35. structure as claimed in claim 34 is characterized in that, the described substrate layer that is cooled reduced the temperature of outside tissue layer before heating pulse.
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| PCT/IB2000/001036 WO2001062170A1 (en) | 2000-02-22 | 2000-02-22 | Method and apparatus for superficial skin heat treatment |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN1460008A true CN1460008A (en) | 2003-12-03 |
Family
ID=11003953
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN00819955.8A Pending CN1460008A (en) | 2000-02-22 | 2000-02-22 | Method and apparatus for superficial skin heat treatment |
Country Status (5)
| Country | Link |
|---|---|
| EP (1) | EP1274359A1 (en) |
| JP (1) | JP2004504074A (en) |
| CN (1) | CN1460008A (en) |
| AU (1) | AU6462200A (en) |
| WO (1) | WO2001062170A1 (en) |
Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN102596117A (en) * | 2009-07-03 | 2012-07-18 | 瓦格纳国际股份公司 | Thermal treatment system and apparatus with biofeedback-driven protocol |
| US9237853B2 (en) | 2009-07-03 | 2016-01-19 | Thermomend International Ltd. | System for detection and treatment of infection or inflammation |
| CN105303043A (en) * | 2015-10-26 | 2016-02-03 | 中国科学院上海硅酸盐研究所 | Data processing method for reducing finite pulse time effects in laser flash method |
| US10265114B2 (en) | 2009-07-03 | 2019-04-23 | Levi Emmerik A. Dewaegenaere | System and method for controlling the operation of a therapeutic pad |
| CN110394831A (en) * | 2019-08-14 | 2019-11-01 | 浙江美森电器有限公司 | A kind of electric arc hair removing apparatus |
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP1671162B1 (en) * | 2003-10-09 | 2014-01-01 | Kilolambda Technologies Ltd. | Optical hot tip |
| DE102006023186B4 (en) * | 2006-05-17 | 2012-02-23 | Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. | Transdermal therapeutic system |
| US8262302B1 (en) * | 2011-12-20 | 2012-09-11 | Elc Management Llc | Kit for a heating applicator and product |
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5968038A (en) * | 1996-10-31 | 1999-10-19 | University Of South Florida | Laser powered heating elements |
| NL1004851C2 (en) * | 1996-12-20 | 1998-06-23 | Gijsbe Gerardus Henricus Maria | Device for ablation and removal of organic tissue |
| US5830208A (en) * | 1997-01-31 | 1998-11-03 | Laserlite, Llc | Peltier cooled apparatus and methods for dermatological treatment |
| EP1042033A1 (en) * | 1997-12-23 | 2000-10-11 | ESC Medical Systems Ltd. | Apparatus for therapeutic electromagnetic treatment |
| US6165170A (en) * | 1998-01-29 | 2000-12-26 | International Business Machines Corporation | Laser dermablator and dermablation |
| US6569157B1 (en) * | 1998-05-18 | 2003-05-27 | Abbott Laboratories | Removal of stratum corneum by means of light |
-
2000
- 2000-02-22 EP EP00951775A patent/EP1274359A1/en not_active Withdrawn
- 2000-02-22 JP JP2001561240A patent/JP2004504074A/en active Pending
- 2000-02-22 CN CN00819955.8A patent/CN1460008A/en active Pending
- 2000-02-22 WO PCT/IB2000/001036 patent/WO2001062170A1/en not_active Application Discontinuation
- 2000-02-22 AU AU64622/00A patent/AU6462200A/en not_active Abandoned
Cited By (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN102596117A (en) * | 2009-07-03 | 2012-07-18 | 瓦格纳国际股份公司 | Thermal treatment system and apparatus with biofeedback-driven protocol |
| US9237853B2 (en) | 2009-07-03 | 2016-01-19 | Thermomend International Ltd. | System for detection and treatment of infection or inflammation |
| CN102596117B (en) * | 2009-07-03 | 2016-01-20 | 瓦格纳国际股份公司 | There is heat treatment system and the instrument of biofeedback drive scheme |
| US10265114B2 (en) | 2009-07-03 | 2019-04-23 | Levi Emmerik A. Dewaegenaere | System and method for controlling the operation of a therapeutic pad |
| CN105303043A (en) * | 2015-10-26 | 2016-02-03 | 中国科学院上海硅酸盐研究所 | Data processing method for reducing finite pulse time effects in laser flash method |
| CN105303043B (en) * | 2015-10-26 | 2018-04-03 | 中国科学院上海硅酸盐研究所 | Reduce the data processing method of laser flash method effect of heating-pulse width |
| CN110394831A (en) * | 2019-08-14 | 2019-11-01 | 浙江美森电器有限公司 | A kind of electric arc hair removing apparatus |
Also Published As
| Publication number | Publication date |
|---|---|
| EP1274359A1 (en) | 2003-01-15 |
| JP2004504074A (en) | 2004-02-12 |
| AU6462200A (en) | 2001-09-03 |
| WO2001062170A1 (en) | 2001-08-30 |
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